System and method for checking high power microwave ablation system status on startup

ABSTRACT

A microwave ablation system includes a generator operable to output energy and an ablation probe coupled to the generator that delivers the energy to a tissue region. The ablation system also includes a controller operable to control the generator and at least one sensor coupled to the ablation probe and the controller that detects an operating parameter of the ablation probe. The controller performs a system check by ramping up an energy output of the generator from a low energy level to a high energy level and monitors an output from the sensor at predetermined intervals of time during the system check to determine an abnormal state. The controller controls the generator to cease the energy output when the controller determines an abnormal state.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a divisional of U.S. patent application Ser.No. 12/562,575, filed Sep. 18, 2009, the entire contents of which arehereby incorporated by reference herein.

BACKGROUND

1. Technical Field

The present disclosure relates generally to microwave ablationprocedures that utilize microwave surgical devices having a microwaveantenna which may be inserted directly into tissue for diagnosis andtreatment of diseases. More particularly, the present disclosure isdirected a system and method for verifying correct system operationprior to high power energy delivery by the microwave antenna.

2. Background of Related Art

In the treatment of diseases such as cancer, certain types of cancercells have been found to denature at elevated temperatures (which areslightly lower than temperatures normally injurious to healthy cells.)These types of treatments, known generally as hyperthermia therapy,typically utilize electromagnetic radiation to heat diseased cells totemperatures above 41° C., while maintaining adjacent healthy cells atlower temperatures where irreversible cell destruction will not occur.Other procedures utilizing electromagnetic radiation to heat tissue alsoinclude ablation and coagulation of the tissue. Such microwave ablationprocedures, e.g., such as those performed for menorrhagia, are typicallydone to ablate and coagulate the targeted tissue to denature or kill thetissue. Many procedures and types of devices utilizing electromagneticradiation therapy are known in the art. Such microwave therapy istypically used in the treatment of tissue and organs such as theprostate, heart, liver, lung, kidney, and breast.

One non-invasive procedure generally involves the treatment of tissue(e.g., a tumor) underlying the skin via the use of microwave energy. Themicrowave energy is able to non-invasively penetrate the skin to reachthe underlying tissue. However, this non-invasive procedure may resultin the unwanted heating of healthy tissue. Thus, the non-invasive use ofmicrowave energy requires a great deal of control.

Presently, there are several types of microwave probes in use, e.g.,monopole, dipole, and helical. One type is a monopole antenna probe,which consists of a single, elongated microwave conductor exposed at theend of the probe. The probe is typically surrounded by a dielectricsleeve. The second type of microwave probe commonly used is a dipoleantenna, which consists of a coaxial construction having an innerconductor and an outer conductor with a dielectric junction separating aportion of the inner conductor. The inner conductor may be coupled to aportion corresponding to a first dipole radiating portion, and a portionof the outer conductor may be coupled to a second dipole radiatingportion. The dipole radiating portions may be configured such that oneradiating portion is located proximally of the dielectric junction, andthe other portion is located distally of the dielectric junction. In themonopole and dipole antenna probe, microwave energy generally radiatesperpendicularly from the axis of the conductor.

The typical microwave antenna has a long, thin inner conductor thatextends along the axis of the probe and is surrounded by a dielectricmaterial and is further surrounded by an outer conductor around thedielectric material such that the outer conductor also extends along theaxis of the probe. In another variation of the probe that provides foreffective outward radiation of energy or heating, a portion or portionsof the outer conductor can be selectively removed. This type ofconstruction is typically referred to as a “leaky waveguide” or “leakycoaxial” antenna. Another variation on the microwave probe involveshaving the tip formed in a uniform spiral pattern, such as a helix, toprovide the necessary configuration for effective radiation. Thisvariation can be used to direct energy in a particular direction, e.g.,perpendicular to the axis, in a forward direction (i.e., towards thedistal end of the antenna), or combinations thereof.

Invasive procedures and devices have been developed in which a microwaveantenna probe may be either inserted directly into a point of treatmentvia a normal body orifice or percutaneously inserted. Such invasiveprocedures and devices potentially provide better temperature control ofthe tissue being treated. Because of the small difference between thetemperature required for denaturing malignant cells and the temperatureinjurious to healthy cells, a known heating pattern and predictabletemperature control is important so that heating is confined to thetissue to be treated. For instance, hyperthermia treatment at thethreshold temperature of about 41.5° C. generally has little effect onmost malignant growth of cells. However, at slightly elevatedtemperatures above the approximate range of 43° C. to 45° C., thermaldamage to most types of normal cells is routinely observed. Accordingly,great care must be taken not to exceed these temperatures in healthytissue.

In the case of tissue ablation, a high radio frequency electricalcurrent in the range of about 500 mHz to about 10 gHz is applied to atargeted tissue site to create an ablation volume, which may have aparticular size and shape. Ablation volume is correlated to antennadesign, antenna performance, antenna impedance and tissue impedance. Theparticular type of tissue ablation procedure may dictate a particularablation volume in order to achieve a desired surgical outcome. By wayof example, and without limitation, a spinal ablation procedure may callfor a longer, narrower ablation volume, whereas in a prostate ablationprocedure, a more spherical ablation volume may be required.

Microwave ablation devices utilize sensors to determine if the system isworking properly. However, without delivery of microwave energy, thesensors may indicate that the probe assembly status is normal. Further,defects in antenna assemblies may not be apparent except at high powers.As such, when microwave ablation system is tested using a low powerroutine a post manufacture defect may not be apparent. This isespecially important for high power microwave ablation devices, wherefailures may result in extremely high temperatures.

SUMMARY

The present disclosure provides a microwave ablation system. Themicrowave ablation system includes a generator operable to outputenergy, an ablation probe coupled to the generator that is operable todeliver the energy to a tissue region, a controller operable to controlthe generator, and at least one sensor coupled to the ablation probe andthe controller. The sensor detects an operating parameter of theablation probe. The controller performs a system check by ramping up anenergy output of the generator from a low energy level to a high energylevel and monitors an output from the at least one sensor atpredetermined intervals of time during the system check to determine anabnormal state. The controller controls the generator to cease theenergy output when the controller determines an abnormal state.

In another embodiment of the microwave ablation system, the at least onesensor detects a temperature of the ablation probe.

In yet another embodiment of the microwave ablation system, the at leastone sensor is a thermocouple, thermistor, or optical fiber.

In yet another embodiment of the microwave ablation system, the at leastone sensor detects a radiating behavior.

In yet another embodiment of the microwave ablation system, the at leastone sensor is a receiving antenna or rectenna.

In yet another embodiment of the microwave ablation system, the at leastone sensor detects forward and/or reflected power.

In yet another embodiment of the microwave ablation system, the at leastone sensor is a radio frequency power sensor.

In yet another embodiment of the microwave ablation system, the at leastone sensor detects fluid pressure.

In yet another embodiment of the microwave ablation system, the at leastone sensor is a pressure sensor.

In yet another embodiment of the microwave ablation system, the at leastone sensor detects air bubbles.

In yet another embodiment of the microwave ablation system, the at leastone sensor is an optical sensor.

The present disclosure also provides a method of detecting an abnormalstate in a microwave ablation system. The method includes the steps ofoutputting a low energy level from a generator to an ablation probe anddetecting an operational parameter of the ablation probe at the lowenergy level. The detected operational parameter is compared to apredetermined range for the operational parameter and an energy leveloutput of the generator is increased in response to the comparison. Themicrowave ablation system ceases output of energy from the generator inresponse to the detected operational parameter being outside thepredetermined range.

In yet another embodiment, the operational parameter is a temperature ofthe ablation probe.

In yet another embodiment, the operational parameter is a radiatingbehavior.

In yet another embodiment, the operational parameter is forward power orreflected power.

In yet another embodiment, the operational parameter is fluid pressure.

In yet another embodiment, the operational parameter is the presence ofair bubbles.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects, features, and advantages of the presentdisclosure will become more apparent in light of the following detaileddescription when taken in conjunction with the accompanying drawings inwhich:

FIG. 1 shows a representative diagram of a variation of a microwaveantenna assembly in accordance with an embodiment of the presentdisclosure;

FIG. 2 shows a cross-sectional view of a representative variation of adistal end of microwave antenna assembly in accordance with anotherembodiment of the present disclosure;

FIG. 3 shows a cross-sectional view of a representative variation of aproximal end of microwave antenna assembly in accordance with anotherembodiment of the present disclosure;

FIGS. 4A-4D show perspective views of an embodiment of a distal portionof a microwave antenna in various stages of assembly;

FIGS. 5A-5C show graphs of time versus power in accordance withembodiments of the present disclosure;

FIG. 6 shows a system block diagram according to an embodiment of thepresent disclosure; and

FIG. 7 shows a flow chart describing a ramping procedure according to anembodiment of the present disclosure.

DETAILED DESCRIPTION

Particular embodiments of the present disclosure are describedhereinbelow with reference to the accompanying drawings; however, it isto be understood that the disclosed embodiments are merely exemplary ofthe disclosure and may be embodied in various forms. Well-knownfunctions or constructions are not described in detail to avoidobscuring the present disclosure in unnecessary detail. Therefore,specific structural and functional details disclosed herein are not tobe interpreted as limiting, but merely as a basis for the claims and asa representative basis for teaching one skilled in the art to variouslyemploy the present disclosure in virtually any appropriately detailedstructure. Like reference numerals may refer to similar or identicalelements throughout the description of the figures.

Electromagnetic energy is generally classified by increasing energy ordecreasing wavelength into radio waves, microwaves, infrared, visiblelight, ultraviolet, X-rays and gamma-rays. As used herein, the term“microwave” generally refers to electromagnetic waves in the frequencyrange of 300 megahertz (MHz) (3×10⁸ cycles/second) to 300 gigahertz(GHz) (3×10¹¹ cycles/second). As used herein, the term “RF” generallyrefers to electromagnetic waves having a lower frequency thanmicrowaves. The phrase “ablation procedure” generally refers to anyablation procedure, such as RF or microwave ablation or microwaveablation assisted resection. The phrase “transmission line” generallyrefers to any transmission medium that can be used for the propagationof signals from one point to another.

FIG. 1 shows a microwave antenna assembly 100 in accordance with oneembodiment of the present disclosure. Antenna assembly 100 includes aradiating portion 12 that is connected by feedline 110 (or shaft) viacable 15 to connector 16, which may further connect the assembly 10 to apower generating source 28, e.g., a microwave or RF electrosurgicalgenerator. Assembly 100, as shown, is a dipole microwave antennaassembly, but other antenna assemblies, e.g., monopole or leaky waveantenna assemblies, may also utilize the principles set forth herein.Distal radiating portion 105 of radiating portion 12 includes a taperedend 120 which terminates at a tip 123 to allow for insertion into tissuewith minimal resistance. It is to be understood, however, that taperedend 120 may include other shapes, such as without limitation, a tip 123that is rounded, flat, square, hexagonal, cylindroconical or any otherpolygonal shape.

An insulating puck 130 is disposed between distal radiating portion 105and proximal radiating portion 140. Puck 130 may be formed from anysuitable elastomeric or ceramic dielectric material by any suitableprocess. In embodiments, the puck 130 is formed by overmolding frompolyether block amide (e.g., Pebax® sold by Arkema), polyetherimide(e.g., Ultem® and/or Extern® sold by SABIC Innovative Plastics),polyimide-based polymer (e.g., Vespel® sold by DuPont), or ceramic. Asbest illustrated in FIG. 2, puck 130 includes coolant inflow port 131and coolant outflow port 133 to respectively facilitate the flow ofcoolant into, and out of, coolant chamber 148 of trocar 122 as furtherdescribed hereinbelow.

With reference now to FIGS. 2, 3, and 4A-4D, distal radiating portion105 includes a trocar 122 having a generally cylindroconical shape.Proximal radiating portion 140 includes a proximal antenna member 128having a generally cylindrical shape. Additionally or alternatively,proximal antenna member 128 may have a generally square or hexagonalshape. Trocar 122 and proximal antenna member 128 may be formed from avariety of biocompatible heat resistant conductive materials suitablefor penetrating tissue, such as without limitation, stainless steel.Antenna assembly 110 includes a coaxial transmission line 138 having, incoaxial disposition, an inner coaxial conductor 150, an intermediatecoaxial dielectric 132, and an outer coaxial conductor 134. Nominally,coaxial transmission line 138 has an impedance of about 50 ohms. Innercoaxial conductor 150 and outer coaxial conductor 134 may be formed fromany suitable electrically conductive material. In some embodiments,inner coaxial conductor 150 is formed from stainless steel and outercoaxial conductor 132 is formed from copper. Coaxial dielectric 132 maybe formed from any suitable dielectric material, including withoutlimitation, polyethylene terephthalate, polyimide, orpolytetrafluoroethylene (PTFE) (e.g., Teflon®, manufactured by E. I. duPont de Nemours and Company of Wilmington, Del., United States). Innercoaxial conductor 150 may be electrically coupled to trocar 122 andouter coaxial conductor 134 may be electrically coupled to proximalantenna member 128.

A longitudinal opening 146 is defined within trocar 122 and opens to aproximal end thereof, and defines a cooling chamber 148 and a threadedsection 145 within trocar 122. Cooling chamber 148 may have a generallycylindrical shape and, additionally or alternatively, may have astepped, tapered, conical, or other shape that is generally dimensionedin accordance with the shape of the tapered end 120 of thecylindroconical profile of trocar 122 to permit the flow of coolant tomore effectively reach the distal regions of trocar 122. Additionally oralternatively, cooling chamber may have a square, hexagonal, or anysuitable shape. The dielectric properties of sterile water or salineflowing through cooling chamber 148 may enhance the overall ablationpattern of antenna 100.

A coolant inflow tube 126 is in operable fluid communication at aproximal end thereof with a source of cooling fluid (not explicitlyshown), and, at a distal end thereof, coolant inflow tube 126 is influid communication with cooling chamber 146 to provide coolant thereto.Coolant inflow tube 126 may be formed from any suitable material, e.g.,a polymeric material, such as without limitation, polyimide. In anembodiment, coolant inflow tube 126 passes through coolant inflow port131. In some embodiments, a coolant outflow channel 136 may be providedto facilitate removal of coolant from cooling chamber 146, throughantenna assembly 100, to a collection reservoir (not explicitly shown).The coolant may be any suitable fluid, such as without limitation water,sterile water, deionized water, and/or saline.

Threaded section 145 of trocar 122 is configured to receive trocar screw144. Trocar screw 144 includes at the proximal end thereof an opening143 defined therein that is configured to accept the distal end of innercoaxial conductor 150. In embodiments, distal end of inner coaxialconductor 150 is fixed within opening 143 by any suitable manner ofelectromechanical attachment, such as without limitation welding,brazing, and/or crimping. As seen in FIG. 4A, an inflow groove 147 andan outflow groove 149 are disposed longitudinally through the threadedportion of trocar screw 144 to respectively facilitate the flow ofcoolant into, and out of, cooling chamber 148. Inflow groove 147 andoutflow groove 149 may be configured to accommodate the insertion ofcoolant inflow tube 126 and/or a corresponding outflow tube (notexplicitly shown). A return path 156 in the antenna assembly mayadditionally or alternatively provide an exit conduit for the coolingfluid.

In the illustrated embodiment, trocar 122 and proximal antenna member128 include a dielectric coating 121, 127, respectively, on therespective outer surfaces thereof. The dielectric coating 121, 127 mayinclude any suitable dielectric material, such as without limitation,ceramic material. In some embodiments, dielectric coating 121, 127 maybe formed from titanium dioxide and/or zirconium dioxide. Dielectriccoating 121, 127 may be applied to trocar 122 and/or proximal antennamember 128 by any suitable process, for example without limitation,plasma spraying or flame spraying. In embodiments, dielectric coating121, 127 has a thickness in the range of about 0.005 inches to about0.015 inches. During an ablation procedure, the dielectric coating 121,127 may provide improved dielectric matching and/or improved dielectricbuffering between the antenna and tissue, which may enable the use ofhigher power levels, which, in turn, may enable a surgeon to achievegreater ablation rates resulting in increased ablation size, reducedoperative times, and/or improved operative outcomes.

An outer jacket 124 is disposed about the outer cylindrical surface ofantenna assembly 100, e.g., the distal radiating portion 105, puck 130,and proximal radiating section 140. Outer jacket 124 may be formed fromany suitable material, including without limitation polymeric or ceramicmaterials. In some embodiments, outer jacket 124 is formed from PTFE.Outer jacket 124 may be applied to antenna assembly 100 by any suitablemanner, including without limitation, heat shrinking.

Continuing with reference to FIGS. 4A-4D, a method of manufacturingantenna assembly 100 is disclosed wherein inner coaxial conductor 150 isinserted into opening 143 of trocar screw 144. Inner coaxial conductor150 is electrically fixed to trocar screw 144 by any suitable manner ofbonding, such as without limitation, laser welding, brazing, orcrimping. The coaxial transmission line 138 and trocar screw 144subassembly is placed in a mold (not explicitly shown), such as withoutlimitation an injection micro-mold, that is configured to overmold thepuck 130. Advantageously, inflow groove 147 and outflow groove 149 arealigned with mold features (not explicitly shown) corresponding tocoolant inflow port 131 and coolant outflow port 133 such that, whenmolded, a continuous fluid connection is formed between inflow groove147 and coolant inflow port 131, and between outflow groove 149 andoutflow port 133.

Puck material, e.g., ceramic, Pebax®, Ultem®, Extem®, Vespel®, or anysuitable polymer having dielectric properties, is shot into the mold,allowed to cool/and or set, and subsequently released from the mold toform an assembly that includes puck 130, trocar screw 143 and coaxialtransmission line 138 as best illustrated in FIG. 4B. The formed puck130 includes a center section 137 having an outer diameter correspondingto the outer diameters of trocar 122 (inclusive of the thickness ofdielectric coating 121) and/or proximal antenna member 128 (inclusive ofthe thickness of dielectric coating 127). Puck 130 further includes adistal shoulder 141 having an outer diameter corresponding to the innerdiameter of trocar 122, and a proximal shoulder 139 having an outerdiameter corresponding to the inner diameter of proximal antenna member128.

Trocar 122 may then be threaded onto trocar screw 144 to form the distalradiating section 120, as best shown in FIG. 4C. Inflow tube 126 maythen be inserted into coolant inflow port 131. Proximal antenna member128 may then be positioned against puck 130 such that the distal end ofproximal antenna member 128 engages the proximal shoulder of puck 130,thus forming a sealed proximal radiation section 140.

Tension may be applied to inner coaxial conductor 150 and/or dielectric132 in a proximal direction, thereby drawing together distal radiatingsection 105, puck 130, and proximal radiating section 140, and placingpuck 130 in a state of compression. Inner coaxial conductor 150 and/ordielectric 132 may be fixed in a state of tension at an anchor point151, by any suitable manner of fixation, including without limitationspot welding, brazing, adhesive, and/or crimping. In this manner, theantenna sections are “locked” together by the tensile force of innercoaxial conductor 150 and/or dielectric 132, which may result inimproved strength and stiffness of the antenna assembly.

Outer jacket 124 may be applied to the outer surface of radiatingportion 12 by any suitable method, for example without limitation, heatshrinking, overmolding, coating, spraying, dipping, powder coating,baking and/or film deposition.

It is contemplated that the steps of a method in accordance with thepresent disclosure can be performed in a different ordering than theordering provided herein.

FIG. 5A is a graph depicting an operation of the microwave ablationsystem according to an embodiment of the invention. As depicted in FIG.5, at t=0, the energy output from the generator is W_(L) that may be alow wattage or 0 W. As t increases, the energy output also increases ata constant slope A. Slope A is sufficient to prevent any harm to aclinician or patient and to prevent and damage to the system. Whent=ramp, with ramp being a value of time sufficient to determine if themicrowave ablation system is malfunctioning, the energy output increasesto an energy level, e.g., 140 W, sufficient to perform a microwaveablation procedure. During the ramping procedure (0<t<ramp), themicrowave ablation system performs a system check to determine if thesystem is in proper working order or if it is malfunctioning. If thesystem is malfunctioning, an energy output from the generator is ceasedthereby preventing any harm to a clinician or patient or preventing anyfurther damage to the microwave ablation system.

Alternatively, as shown in FIGS. 5B and 5C, a series of pulses may beused during the start up procedure. As shown in FIG. 5B, the series ofpulses have a constant amplitude with a pulse width T_(W). A duty cyclefor the pulses may be varied in order to adequately check the systemwithout harming the patient or the clinician. Alternatively, as shown inFIG. 5C, the series of pulses during the start up procedure may have apulse width T_(W) and vary in amplitude. The amplitude of the pulses maygradually reach an energy level sufficient to perform a microwaveablation procedure.

By utilizing a system check which gradually subjects the device toincreasing operational stresses while monitoring sensor status willallow for microwave ablation systems to limit the number of deviceswhich are damaged due to operator error, such as not turning on thecooling fluid pump. It will also reduce the likely hood of patientand/or user injury from potentially defective assemblies or from usererror.

With reference to FIG. 6, a microwave ablation system, shown generallyas 600, according to an embodiment of the disclosure is depicted. System600 has an antenna assembly 610 that imparts microwave energy to apatient. Antenna assembly 610 is substantially similar to antennaassembly 100 described above. Generator 620, which is substantiallysimilar to power generating source 28, is coupled to antenna assembly610 and provides a source of energy thereto. Controller 630 is coupledto generator 620 and is configured to control generator 620 based on aninput or signal from sensor 640. Controller 630 may be a microprocessoror any logic circuit able to receive an input or signal from sensor 640and provide an output to control generator 620. Sensor 640 may be asingle sensor or an array of sensors to detect operational parameters ofthe antenna assembly 610 in order to determine if the microwave ablationsystem 600 is functioning properly. If the sensor 640 detects anabnormal value or level, the controller 630 controls the generator 620to cease an energy output. Sensor 640 may be incorporated into antennaassembly 610 or controller 630 or may be coupled to either antennaassembly 610 and/or controller 630. Microwave ablation system 600 mayalso be incorporated in antenna assembly 610 or may be arranged in twoor more devices. For instance, controller 630 and generator 620 may beincorporated in a single device or may be separate devices.

Sensor 640 may be a temperature sensor to detect the temperature of theantenna assembly 610. Temperature sensor may be a thermocouple,thermistor or an optical fiber. A thermocouple is a junction between twodifferent metals that produces a voltage related to a temperaturedifference. Thermocouples are can also be used to convert heat intoelectric power. Any circuit made of dissimilar metals will produce atemperature-related difference of voltage. Thermocouples for practicalmeasurement of temperature are made of specific alloys, which incombination have a predictable and repeatable relationship betweentemperature and voltage. Different alloys are used for differenttemperature ranges and to resist corrosion. Where the measurement pointis far from the measuring instrument, the intermediate connection can bemade by extension wires, which are less costly than the materials usedto make the sensor. Thermocouples are standardized against a referencetemperature of 0 degrees Celsius. Electronic instruments can alsocompensate for the varying characteristics of the thermocouple toimprove the precision and accuracy of measurements.

A thermistor is a type of resistor whose resistance varies withtemperature. Thermistors are widely used as inrush current limiters,temperature sensors, self-resetting overcurrent protectors, andself-regulating heating elements. The material used in a thermistor isgenerally a ceramic or polymer. Thermistors typically achieve a highprecision temperature response within a limited temperature range.

Sensor 640 may also be used to monitor radiating behavior. Such sensormay be a receiving antenna or a rectenna. The receiving antenna receivesradiation from the antenna assembly and provides an electrical signal toindicate the level of radiation. A rectenna is a rectifying antenna, aspecial type of antenna that is used to directly convert microwaveenergy into DC electricity. Its elements are usually arranged in a multielement phased array with a mesh pattern reflector element to make itdirectional. A simple rectenna can be constructed from a Schottky diodeplaced between antenna dipoles. The diode rectifies the current inducedin the antenna by the microwaves.

Sensor 640 may also be an RF power sensor to monitor forward andreflected power. The RF power sensor measures the power output of thegenerator 620 that is utilized by the antenna assembly 610. It can alsomeasure reflected power which is RF energy that is reflected from theablated tissue region and received by the antenna assembly.

Sensor 640 may also be a pressure sensor for monitoring fluid and/or gaspressure. Pressure sensor generates a signal related to the pressureimposed. Typically, such a signal is electrical, but optical, visual,and auditory signals are not uncommon. Pressure sensors can beclassified in term of pressure ranges they measure, temperature rangesof operation, and most importantly the type of pressure they measure. Interms of pressure type, pressure sensors can be divided into fivecategories. Absolute pressure sensor which measures the pressurerelative to perfect vacuum pressure (0 PSI or no pressure). Gaugepressure sensor is used in different applications because it can becalibrated to measure the pressure relative to a given atmosphericpressure at a given location. Vacuum pressure sensor is used to measurepressure less than the atmospheric pressure at a given location.Differential pressure sensor measures the difference between two or morepressures introduced as inputs to the sensing unit. Differentialpressure is also used to measure flow or level in pressurized vessels.Sealed pressure sensor is similar to the gauge pressure sensor exceptthat it is previously calibrated by manufacturers to measure pressurerelative to sea level pressure.

Sensor 640 may also be an optical sensor to detect air bubbles or fluidflow. For instance, a light source (not shown) emits a light through thecoolant tube in the antenna assembly. The emitted light is reflected bythe coolant and is received by an optical sensor. This reflected lightis compared to the emitted light and a determination is made as to thepresence of an air bubble.

With reference to FIGS. 6 and 7, an operation of the ramping procedureis shown. The procedure starts at S702 where the microwave ablationsystem 600 is started. At S704, T is set to T₀ where T is time and T₀ isthe initial startup time. At S706, a low energy level is outputted fromthe generator 620 to the antenna assembly 610. Sensor 640 detects anoperational parameter of the ablation probe as described above in S708.In S710, the detected operational parameter is compared to apredetermined range of values stored in controller 630. Thepredetermined range of values may be set by a clinician or they may bestored in the controller or they may be stored in the microwave or RFprobe itself by a manufacturer of the microwave ablation system. If thedetected operational parameter is within the predetermined range, theprocedure proceeds to S12 where a determination is made as to whether Tis less than T_(RAMP). If T is less than T_(RAMP), then the procedureproceeds to S714 where T is increased in predetermined intervals. T canbe increased in intervals of N seconds or N minutes where N is anypositive integer. In S716 the energy level output of the generator 620is increased and steps S708, S710 and S712 are repeated. When T is nolonger less than T_(RAMP), the procedures proceeds to S720 where theablation procedure is started and used on a patient. If the controllermakes a determination in S710 that the detected operational parameter inS708 is not within the predetermined range, the procedure proceeds toS718 where the controller 630 controls the generator 620 to cease energyoutput.

The ramping procedure outlined above may avoid an assembly failure andpotential clinician or patient injury. Although FIG. 7 depicts aparticular arrangement of steps to perform the system check during aramping procedure, it should be understood that a different arrangementof steps may be used while still falling under the scope of the presentdisclosure. During the ramping procedure and upon detection of abnormalsensor information, the power ramp would cease and return to zero. Theramp may be made long enough to reliably detect common malfunctionmechanisms.

For instance, if the cooling fluid pump is turned off and no fluid is inthe antenna assembly, a pressure sensor may return abnormal pressurelevels. As such, a power ramp would cease and the power does not reach alevel where the coaxial cable would fail due to lack of cooling. If theantenna assembly is full of cooling fluid but the pump is not running,an abnormal reading from the pressure sensor or a rising temperaturefrom a thermo probe would indicate that cooling of the probe is notsufficient most likely due to lack of flow. Therefore, the power rampwould cease and the power does not reach a level where the coaxial cablewould fail due to lack of circulation.

In another example, if the device is not inserted into tissue resultingin a dangerous radiation pattern, a radiating detector such as thereceiving antenna or rectenna would indicate abnormally high radiatinglevels along the shaft or around the handle of the antenna. Thedetection of the high radiating levels would prevent an unintendedclinician or patient burn.

When the antenna assembly is subjected to high powers, defects maybecome readily apparent. On ramp up, the sensors indicate abnormaloperating conditions thereby preventing the power level from reaching alevel sufficient to cause catastrophic device failure and avoidingclinician or patient injury.

Utilizing a test routine of the ablation probe which gradually subjectsthe device to increasing operational stresses while monitoring sensorstatus will allow for MWA systems to limit the number of devices whichare damaged due to operator error, such as not turning on the coolingfluid pump. It will also reduce the likely hood of patient and/or userinjury from potentially defective assemblies or from user error. This isespecially important for high power microwave ablation devices, wherefailures may result in extremely high temperatures.

The described embodiments of the present disclosure are intended to beillustrative rather than restrictive, and are not intended to representevery embodiment of the present disclosure. Various modifications andvariations can be made without departing from the spirit or scope of thedisclosure as set forth in the following claims both literally and inequivalents recognized in law.

1. A microwave ablation system, comprising: a generator operable tooutput microwave energy; an ablation probe coupled to the generator, theablation probe operable to deliver energy to tissue; a controlleroperable to control the generator; and at least one sensor coupled tothe ablation probe and the controller, the at least one sensor operableto detect an operating parameter of the ablation probe, wherein thecontroller is operable to increase a microwave energy level output ofthe generator at a constant rate from a low microwave energy level to apredetermined microwave energy level and monitor an output from the atleast one sensor while the microwave energy level is increased at theconstant rate, and wherein the controller is operable to control thegenerator to cease the energy output when the controller determines thatthe operating parameter is outside a predetermined range.
 2. Themicrowave ablation system according to claim 1, wherein the at least onesensor detects a temperature of the ablation probe.
 3. The microwaveablation system according to claim 2, wherein the at least one sensor isa thermocouple, thermistor, or optical fiber.
 4. The microwave ablationsystem according to claim 1, wherein the at least one sensor detects aradiating behavior.
 5. The microwave ablation system according to claim4, wherein the at least one sensor is a receiving antenna or rectenna.6. The microwave ablation system according to claim 1, wherein the atleast one sensor detects forward and/or reflected power.
 7. Themicrowave ablation system according to claim 6, wherein the at least onesensor is a radio frequency power sensor.
 8. The microwave ablationsystem according to claim 1, wherein the at least one sensor detectsfluid pressure.
 9. The microwave ablation system according to claim 8,wherein the at least one sensor is a pressure sensor.
 10. The microwaveablation system according to claim 1, wherein the at least one sensordetects air bubbles.
 11. The microwave ablation system according toclaim 10, wherein the at least one sensor is an optical sensor. 12-17.(canceled)